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EP2842508A1 - Bestimmung von kontaktlosen Zuständen für einen Katheter - Google Patents

Bestimmung von kontaktlosen Zuständen für einen Katheter Download PDF

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Publication number
EP2842508A1
EP2842508A1 EP14182271.8A EP14182271A EP2842508A1 EP 2842508 A1 EP2842508 A1 EP 2842508A1 EP 14182271 A EP14182271 A EP 14182271A EP 2842508 A1 EP2842508 A1 EP 2842508A1
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EP
European Patent Office
Prior art keywords
probe
force
period
sensor
predetermined
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Granted
Application number
EP14182271.8A
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English (en)
French (fr)
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EP2842508B1 (de
Inventor
Doron Moshe Ludwin
Aharon Turgeman
Natan Sharon Katz
Erez Silberschein
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Biosense Webster Israel Ltd
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Biosense Webster Israel Ltd
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Publication of EP2842508A1 publication Critical patent/EP2842508A1/de
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
    • A61B5/061—Determining position of a probe within the body employing means separate from the probe, e.g. sensing internal probe position employing impedance electrodes on the surface of the body
    • A61B5/062—Determining position of a probe within the body employing means separate from the probe, e.g. sensing internal probe position employing impedance electrodes on the surface of the body using magnetic field
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/14—Probes or electrodes therefor
    • A61B18/1492—Probes or electrodes therefor having a flexible, catheter-like structure, e.g. for heart ablation
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/05—Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/053—Measuring electrical impedance or conductance of a portion of the body
    • A61B5/0538—Measuring electrical impedance or conductance of a portion of the body invasively, e.g. using a catheter
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/06—Devices, other than using radiation, for detecting or locating foreign bodies ; determining position of probes within or on the body of the patient
    • A61B5/065—Determining position of the probe employing exclusively positioning means located on or in the probe, e.g. using position sensors arranged on the probe
    • A61B5/068—Determining position of the probe employing exclusively positioning means located on or in the probe, e.g. using position sensors arranged on the probe using impedance sensors
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/103—Detecting, measuring or recording devices for testing the shape, pattern, colour, size or movement of the body or parts thereof, for diagnostic purposes
    • A61B5/107—Measuring physical dimensions, e.g. size of the entire body or parts thereof
    • A61B5/1076—Measuring physical dimensions, e.g. size of the entire body or parts thereof for measuring dimensions inside body cavities, e.g. using catheters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/68—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient
    • A61B5/6846—Arrangements of detecting, measuring or recording means, e.g. sensors, in relation to patient specially adapted to be brought in contact with an internal body part, i.e. invasive
    • A61B5/6885—Monitoring or controlling sensor contact pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
    • A61B2017/00681—Aspects not otherwise provided for
    • A61B2017/00725—Calibration or performance testing
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B34/00—Computer-aided surgery; Manipulators or robots specially adapted for use in surgery
    • A61B34/20—Surgical navigation systems; Devices for tracking or guiding surgical instruments, e.g. for frameless stereotaxis
    • A61B2034/2046—Tracking techniques
    • A61B2034/2051—Electromagnetic tracking systems
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B90/00—Instruments, implements or accessories specially adapted for surgery or diagnosis and not covered by any of the groups A61B1/00 - A61B50/00, e.g. for luxation treatment or for protecting wound edges
    • A61B90/06—Measuring instruments not otherwise provided for
    • A61B2090/064—Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension
    • A61B2090/065—Measuring instruments not otherwise provided for for measuring force, pressure or mechanical tension for measuring contact or contact pressure
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2505/00—Evaluating, monitoring or diagnosing in the context of a particular type of medical care
    • A61B2505/05—Surgical care
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00—Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02—Operational features
    • A61B2560/0223—Operational features of calibration, e.g. protocols for calibrating sensors

Definitions

  • the present invention relates generally to contact determination, and specifically to determination of absence of contact of a catheter with body tissue.
  • an electrode assembly on a catheter carries pressure transducers, which sense contact with tissue and convey signals to a pressure contact module.
  • the module identifies the electrode elements that are associated with the pressure transducer signals and directs an energy generator to convey RF energy to these elements, and not to other elements that are in contact only with blood.
  • U.S. Patent Application Publication 2007/0100332 which is incorporated herein by reference, describes systems and methods for assessing electrode-tissue contact for tissue ablation.
  • An electro-mechanical sensor within the catheter shaft generates electrical signals corresponding to the amount of movement of the electrode within a distal portion of the catheter shaft.
  • An output device receives the electrical signals for assessing a level of contact between the electrode and a tissue.
  • U.S. Patent No. 7,306,593 issued to Keidar et al. , which is incorporated herein by reference, describes a method for ablating tissue in an organ by contacting a probe inside the body with the tissue to be ablated, and measuring one or more local parameters at the contact position using the probe prior to ablating the tissue.
  • a map of the organ is displayed, showing, based on the one or more local parameters, a predicted extent of ablation of the tissue to be achieved for a given dosage of energy applied at the position using the probe.
  • the given dosage of energy is applied to ablate the tissue using the probe, and an actual extent of the ablation at the position is measured using the probe subsequent to ablating the tissue.
  • the measured actual extent of the ablation is displayed on the map for comparison with the predicted extent.
  • Impedance-based methods for assessing catheter-tissue contact typically rely on measurement of the magnitude of the impedance between an electrode on the catheter and a body-surface electrode. When the magnitude is below some threshold, the electrode is considered to be in contact with the tissue. This sort of binary contact indication may be unreliable, however, and is sensitive to changes in the impedance between the body-surface electrode and the skin.
  • U.S. Patent Application Publication Nos. 2008/0288038 and 2008/0275465, both by Saurav et al. which are incorporated herein by reference, describe an electrode catheter system having an electrode adapted to apply electric energy.
  • a measurement circuit adapted to measure impedance may be implemented between the electrode and ground as the electrode approaches a target tissue.
  • a processor or processing units may be implemented to determine a contact condition for the target tissue based at least in part on reactance of the impedance measured by the measurement circuit. In another embodiment, the contact condition may be based on the phase angle of the impedance.
  • An embodiment of the present invention provides a method, including:
  • the measured contact forces may include magnitudes of the contact forces. Alternatively or additionally the measured contact forces may include directions of contact forces.
  • the probe consists of a first probe, and the method further includes:
  • the method may yet further include receiving the first signals and the second signals from the force sensor.
  • the probe includes a magnetic field sensor, the method further including measuring the location coordinates of the probe in response to magnetic fields sensed by the sensor.
  • the probe includes an electrode, the method further including measuring the location coordinates in response to an impedance of current flowing through the electrode.
  • the predetermined limit of the measured contact forces is equal to the predetermined force threshold.
  • apparatus including:
  • a medical ablation procedure such as ablation of heart tissue
  • the ablation is typically provided by a probe comprising an ablation electrode at its distal end.
  • a force sensor may be incorporated into the distal end, but such force sensors known in the art typically drift, i.e., even if the force exerted on the sensor is constant, readings from the sensor change. Such drift may be compensated for by zeroing the sensor periodically, typically before applying ablation energy.
  • the zeroing of the sensor should only be applied if the sensor is not contacting tissue, i.e., the sensor is in a state where the force on it is effectively zero (such a state is typically achieved if the sensor is surrounded by blood in the heart chamber, and is not contacting a heart wall).
  • Embodiments of the present invention detect such a state for the sensor, herein termed a zeroing state.
  • the force sensor is assumed to be in a zeroing state if over at least a predetermined interval of time force readings from the sensor change by less than a predetermined force limit.
  • the probe having the force sensor is typically also assumed to change its location during the predetermined time interval by more than a predetermined location threshold.
  • embodiments of the present invention auto-zero the sensor, i.e., they calibrate a zero-force point for the force sensor.
  • received signals from the sensor are checked to detect a situation wherein the sensor is in a first zeroing state, then in a non-zeroing state (such as if the sensor indicates it is touching tissue), and then in a second zeroing state. Once such a situation is detected, force readings from the second zeroing state may be used as calibration values that zero the sensor.
  • the probe is in proximity to another, second, probe.
  • the inventors have found that changes in proximity between the probes may reduce the accuracy of the calibration values referred to above.
  • the first probe may be assumed to be in the zeroing state if, in addition to the force condition described above, a measured value of the change in proximity is less than a predetermined proximity change threshold.
  • the inventors have found that, from measurements on actual cases using embodiments of the present invention, there is an extremely high probability of auto-zeroing the sensor when the sensor does not contact tissue. In addition, there is an extremely high probability of not auto-zeroing when the sensor does contact tissue.
  • FIG. 1 is a pictorial illustration of a probe system 10 for performing ablative procedures on a heart 12 of a living subject 13, according to an embodiment of the invention.
  • the system comprises a probe 14, typically a catheter, which is percutaneously inserted by an operator 16 through the patient's vascular system into a chamber or vascular structure of the heart.
  • the operator who is typically a physician, brings the probe's distal tip 18 into contact with a heart wall 19 at an ablation target site.
  • electrical activation maps may then be prepared, according to the methods disclosed in U.S. Patent Nos. 6,226,542 , and 6,301,496 , and in commonly assigned U.S. Patent No.
  • Areas determined to be abnormal can be ablated by application of thermal energy, e.g., by passage of radiofrequency electrical current through wires in the probe to one or more electrodes at distal tip 18, which apply the radiofrequency energy to the myocardium.
  • the energy is absorbed in the tissue, heating it to a point (typically about 50°C) at which it permanently loses its electrical excitability.
  • This procedure creates non-conducting lesions in the cardiac tissue, which disrupt the abnormal electrical pathway causing the arrhythmia.
  • the principles of the invention can be applied to different heart chambers to treat many different cardiac arrhythmias.
  • Probe 14 typically comprises a handle 20, having suitable controls on the handle to enable operator 16 to steer, position and orient a distal end 21 of the probe as desired for the ablation. To aid the operator, the distal end of probe 14 contains a position sensor 38 that provides signals to a positioning processor 22, located in a console 24.
  • Ablation energy signals and other electrical signals can be conveyed to and from heart 12 through an electrode 32 located at distal tip 18 via a cable 34 to console 24. Electrode 32 may also be referred to herein as the ablation electrode. There may be other electrodes (not shown) located at the distal end that are used for ablation. Pacing signals and other control signals may be conveyed from the console through cable 34 and electrode 32, or via the other electrodes at the distal end, to the heart; these signals may be conveyed in parallel with any ablation energy signals, typically by using frequency multiplexing for the different signals.
  • Factors affecting the ablation generated by the ablation energy input to the tissue being ablated comprise, inter alia, the contact force applied to the tissue during the ablation process.
  • the distal end of probe 14 comprises a force sensor 36.
  • Force or pressure sensors that are suitable for use in a probe are well known in the art.
  • U.S. Patent Application Publications 2007/0100332 and 2009/0093806 whose disclosures are incorporated herein by reference, describe methods of sensing contact pressure between the distal tip of a probe and tissue in a body cavity using a force or pressure sensor embedded in the probe.
  • force sensor 36 may comprise any other force or pressure sensor known in the art.
  • Wire connections 35 link the console with body surface electrodes 30 and other components of a positioning sub-system. Electrode 32 and body surface electrodes 30 may be used to measure tissue impedance at the ablation site as taught in U.S. Patent No. 7,536,218, issued to Govari et al. , which is herein incorporated by reference.
  • a temperature sensor (not shown), typically a thermocouple or thermistor, may be mounted on or near electrode 32.
  • Positioning processor 22 is an element of a positioning subsystem (of system 10) which measures location and orientation coordinates of probe 14, using position sensor 38.
  • the positioning subsystem comprises a magnetic position tracking arrangement that determines the location and orientation of probe 14 by generating magnetic fields in a predefined working volume in the vicinity of the probe, using field generating coils 28. These fields are sensed by position sensor 38 and the sensed fields are used to determine location and orientation coordinates for the probe.
  • an impedance module 40 is configured to measure an impedance of current flowing between ablation electrode 32 and body electrodes 30. In some cases measurements of the impedance may be used to estimate a location of electrode 32.
  • probe 14 is coupled to console 24, which enables operator 16 to observe and regulate the functions of the probe.
  • Console 24 includes a processor 25, preferably a computer with appropriate signal processing circuits, which operates system 10.
  • Processor 25 is coupled to drive a monitor 29.
  • the signal processing circuits typically receive, amplify, filter and digitize signals from probe 14, including signals generated by the above-noted sensors and a plurality of location sensing electrodes (not shown) located distally in the probe. The digitized signals are received and used by the console and the positioning subsystem to compute the location and orientation of probe 14 and to analyze the electrical signals from the electrodes.
  • the output of the sensor drifts, even though the force on the sensor may be constant.
  • Sensor 36 typically measures the magnitude and direction of the force, and the drift may be in one of these variables, or in both of them.
  • the drift is typically caused by changes in parameters of physical elements associated with the sensor, such as gain changes of amplifiers and/or dimensional changes of parts of the sensor.
  • the drift may be compensated for by zeroing the sensor, but the zeroing should only be performed when there is no contact between the distal tip of the probe and a solid object such as wall 19 of heart 12.
  • Embodiments of the present invention detect periods when no such contact exists, and auto-zero sensor 36 during these periods.
  • a second probe 50 is located within heart 12 so that a distal end 52 of the second probe is in proximity to distal end 21 of the first probe.
  • An electrode 54 is located at a distal tip 56 of the second probe, and the electrode is connected via a cable 58 to console 24.
  • a position sensor 60 is also located within distal end 52 of the second probe.
  • a change of the proximity of distal end 21 of the first probe to distal end 52 of the second probe alters readings of force sensor 36 in the first probe.
  • the altered readings typically reduce the accuracy of, or even completely invalidate, any zero-force point derived from the readings during calibration of the sensor.
  • embodiments of the present invention use readings from force sensor 36 to estimate the proximity of the two distal ends, and to quantify the proximity numerically in a proximity index (PI) parameter.
  • PI proximity index
  • force sensor 36 is only zeroed if a change in the proximity index, ⁇ PI is less than a preset value.
  • Fig. 2 is a first flowchart 100 of steps followed by processor 25 and Fig. 3 is a second flowchart 200 of steps followed by the processor, in auto-zeroing sensor 36, according to embodiments of the present invention.
  • Flowchart 100 is a "high-level” flowchart of the steps followed by the processor in determining when, and with what values, sensor 36 of the first probe is to be auto-zeroed.
  • Flowchart 100 assumes that sensor 36 is in or is not in a "zeroing state.”
  • Flowchart 200 is a "low-level" flowchart, providing the steps used by processor 25 in deciding when sensor 36 is in a zeroing state.
  • processor 25 uses values of force, proximity index, and location that are measured for distal tip 18.
  • the force sensor is able to measure both the magnitude and direction of the force, but for simplicity in the following description, only the magnitude of the force is considered.
  • Those having ordinary skill in the art will be able to adapt the description, mutatis mutandis, to account for changes in the direction of the force, typically by calculating the magnitude of the change of force vector.
  • the processor uses predetermined threshold values for a force change, a proximity index change, a location change, and a time period.
  • the force, proximity index, and location changes, and the time period threshold values are respectively represented by the symbols ⁇ F t , ⁇ PI T , ⁇ L t , and ⁇ T t .
  • ⁇ F t 1g
  • ⁇ PI t 1.5
  • ⁇ L t 10mm
  • ⁇ T t 1000ms.
  • Processor 25 typically runs the two flowcharts in parallel.
  • processor 25 uses measurements of time, force, proximity index and location to identify that force sensor 36 is in a zeroing state.
  • Flowchart 200 provides details of how the measurements are used to determine of the sensor is in a zeroing state.
  • the processor saves initial values of time T init , force F init , proximity index PI init , and location L init . While in step 102, the processor continues to acquire values of the time, the force, the proximity index, and the location.
  • a zeroing state for the force sensor corresponds to a state where values of the time, force, proximity index and location for the sensor indicate that the sensor distal tip of the probe is not in contact with any solid surface, and that the proximity of the two probe distal ends has not changed significantly. However, in a zeroing state there is typically drift in the signal output by the force sensor. As is shown in flowchart 200, the zeroing state corresponds to, for at least predetermined time period ⁇ T t , the force registered by the force sensor changing by less than predetermined force change threshold value ⁇ F t , the distal end moving by more than predetermined distance ⁇ L t , and the proximity index changing by less than predetermined proximity index change threshold ⁇ I t .
  • a termination step 104 the processor uses measurements of the force and of the location to establish that the force sensor is no longer in its zeroing state.
  • the processor invokes termination step 104 if either the force change measured by sensor 36 exceeds ⁇ F t or if the location of distal tip 18 changes by more than ⁇ L t .
  • a change state step 105 the probe enters a change state, where it is no longer in a zeroing state.
  • processor 25 identifies that force sensor 36 is in a second zeroing state, substantially repeating the procedure of step 102. While in the second zeroing state, the processor calculates, on a continuing basis, updated values of force changes, ⁇ F 2 , using an initial force saved on entering step 106 and an equation corresponding to equation (1).
  • a comparison step 108 the processor compares the changes of values of the force of zeroing state step 106 with those saved in step 104. I.e., the processor compares values of ⁇ F 1 and ⁇ F 2 . Providing that the difference of the force changes is within a predetermined limit, typically the predetermined force change threshold ⁇ F t , in an auto-zero step 110 the processor is able to auto-zero the sensor, typically by using the most recent values acquired from the force sensor in step 106 as zero-point values for the sensor. In one embodiment the zero-point values are an average of the most recent signal values taken over a predetermined time period, such as 1s.
  • step 108 If in comparison step 108 the difference of the force changes is not within its predetermined limit, the flowchart returns to step 102, and the processor reiterates the steps of the flowchart.
  • step 108 the processor compares force change values found in step 106 with all of the saved force change values of previous iterations. If any one of the comparisons is valid, then the comparison step 108 is assumed to return positive and the processor uses the values in the second zeroing step to auto-zero the force sensor.
  • Fig. 3 is flowchart 200, which comprises steps performed by processor 25 in deciding if force sensor 36 is in a zeroing state.
  • the force sensor may be in an intermediate state, as explained below.
  • the processor uses threshold values ⁇ F t , ⁇ PI t , ⁇ L t , and ⁇ T t , referred to above.
  • processor 25 For the steps of the flowchart, which mainly comprises comparisons, processor 25 performs each of the steps on a continuing basis so that the sequence of steps is performed reiteratively as a loop. For each loop iteration there is a new value of time, and typically new values of force, location or proximity index.
  • flowchart 200 is implemented as a state machine. From the flowchart description herein, such a state machine will be apparent to those having ordinary skill in the art.
  • step 202 the processor saves initial values of time T init , force F init , proximity index PI init , and location L init .
  • a first comparison step 204 the processor measures a current value of the force F current and a current value of the proximity index PI current .
  • the processor determines if the expression in expression (3) returns true or false: ⁇ F ⁇ ⁇ F t and ⁇ PI ⁇ ⁇ PI t
  • the force comparison and the proximity index comparison are preliminary tests which are typically true if the distal tip is not in contact with wall 19 of the heart, and if the proximity index has not changed appreciably.
  • comparison 208 the processor respectively checks if the sensor has moved by more than the threshold distance ⁇ L t , or if the force has changed by more than the threshold force ⁇ F t .
  • force sensor 36 is in a second waiting state 214 where the force sensor is waiting to move more than the threshold distance ⁇ L t or for the force change to exceed the threshold force ⁇ F t .
  • comparison 208 returns true, the flowchart continues to a fourth comparison 218, wherein the initial values F init and proximity index PI init are updated to the respective values when the processor enters the comparison.
  • the processor checks that, over a time period greater than the time threshold ⁇ T t , the force has changed by less than the force threshold ⁇ F t and the proximity index has changed by less than the proximity index threshold ⁇ PI t .
  • the force sensor is in zeroing state 210 if, for at least a predetermined time period ⁇ T t , the force registered by the force sensor changes by less than predetermined force threshold value ⁇ F t and the proximity index changes by less than predetermined proximity index change threshold ⁇ PI t .
  • the condition of comparison 218 typically only holds if the distal tip does not contact wall 19 of the heart and if there has been no appreciable proximity index change.
  • Fig. 4 is a schematic graph of force magnitude vs. time, according to an embodiment of the present invention.
  • the graph illustrates values of time and the force magnitude, derived from a vectorial force, as measured for distal tip 18. While the time and the force are being measured, location and proximity values for the distal tip are also measured, but for simplicity graphs of these values vs. time are not shown.
  • the force magnitude is measured in grams (g), and the time is measured in seconds (s).
  • the graph is divided into three time periods, T 1 - T 2 , T 2 - T 3 , and T 3 - T 4 , also respectively referred to herein as periods A, B and C.
  • the first two comparisons in expression (4) are illustrated in the graph; the third and fourth comparisons are from measured proximity index and location changes, ⁇ PI A and ⁇ L A , during period A.
  • the graph for periods A and C illustrate the case where distal tip 18 is not in contact with wall 19.
  • Step 110 The situation illustrated by the graph, of a first and second zeroing state separated by a period in time where there is a change of force greater than the threshold force, may be applied to flowchart 100. Steps 102, 104, 105, and 106 all apply. Assuming comparison 108 is valid, then in step 110 the probe is auto-zeroed at time T 4 using values from time period C.

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EP14182271.8A 2013-08-27 2014-08-26 Bestimmung von kontaktlosen Zuständen für einen Katheter Active EP2842508B1 (de)

Applications Claiming Priority (1)

Application Number Priority Date Filing Date Title
US14/010,697 US9949664B2 (en) 2013-08-27 2013-08-27 Determining non-contact state for a catheter

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EP2842508A1 true EP2842508A1 (de) 2015-03-04
EP2842508B1 EP2842508B1 (de) 2019-03-13

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EP (1) EP2842508B1 (de)
JP (1) JP6448951B2 (de)
CN (1) CN104414739B (de)
AU (1) AU2014215986B2 (de)
CA (1) CA2859820A1 (de)
ES (1) ES2727288T3 (de)
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USD748137S1 (en) * 2013-08-20 2016-01-26 Biosense Webster (Israel) Ltd. Portion of a computer screen with an icon
US10363090B2 (en) * 2016-01-05 2019-07-30 Biosense Webster (Israel) Ltd. Catheter with flow diverter and force sensor
EP3435914A1 (de) 2016-03-30 2019-02-06 Koninklijke Philips N.V. Verfahren und system zur kalibrierung einer mundreinigungsvorrichtung
IL254009A0 (en) * 2016-08-18 2017-09-28 Nutriseal Lp A system and method for directing the location of a device inserted into the body
US10548815B2 (en) * 2018-04-30 2020-02-04 Envizion Medical Ltd. Insertion device positioning guidance system and method
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CA2859820A1 (en) 2015-02-27
CN104414739A (zh) 2015-03-18
JP6448951B2 (ja) 2019-01-09
CN104414739B (zh) 2018-10-09
AU2014215986A1 (en) 2015-03-19
JP2015043979A (ja) 2015-03-12
EP2842508B1 (de) 2019-03-13
US9949664B2 (en) 2018-04-24
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AU2014215986B2 (en) 2019-05-16
IL234040B (en) 2018-11-29

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